JP4819045B2 - Defibrillator with cardiac blood flow measurement - Google Patents

Description

  The present invention relates to a method for determining whether an event of cardiac electrical activity is the result of a corresponding blood flow event, and an external defibrillator performing such a method.

  Surviving from sudden cardiac death (SCD) outside the hospital is now a normal occurrence. The most important factor affecting survival is the time between the onset of disease and treatment. Automated external defibrillators (AEDs) have expanded their use on a daily basis because they allow treatment by ambulance and trained personnel in the field rather than having to transport the patient to a medical facility. ing. In recent years, their use has been requested by government agencies in airplanes, some common places and offices. There are medical and public pressures on making it available to family members and smaller facilities.

  Modern defibrillators (AEDs) are compact and portable devices that automatically analyze an electrocardiogram (ECG) obtained from a human chest through electrodes in contact with the skin. A user attempting to respond to an emergency with suspected SCD will simply take an AED, press the “on” button, and follow the voice and text instructions and the instructions issued by the device. A typical sequence of events would be that the device prompts the user to put a pad on the patient's chest and make sure that the electrodes are properly connected to the device. Once the device is satisfied that this has been done, the device will automatically analyze the patient's heart rhythm to make a diagnosis. If the device determines that a high voltage shock is required, it will automatically charge to a predetermined energy level and advise the user to press the clearly labeled “shock” button. Pushing the button delivers energy to the patient through the same electrode used to monitor the ECG. Whether or not the device advises to shock, the user is given continuous information about the patient's condition and / or activity and the condition of the device.

  In order to analyze the patient's ECG, these AEDs use an algorithm that employs various parameters measured from the digitized ECG. These parameters typically also include several integration techniques, such as ECG rhythm frequency and amplitude, and slope, morphology, and heart rate. Many algorithms also use zero content, baseline content, and energy ratio calculations. The mathematical dispersion of several parameters can also be calculated to improve the performance of these devices.

  However, all AEDs using this approach suffer from the fact that they are analyzing ECG or parameters measured from it. There are many references that show how ECG is associated with the mechanical and hemodynamic responses of the heart, but there is ECG activity with little or no cardiac output There are many. Furthermore, the heart rhythm often exhibits a random and unstable nature while maintaining sufficient cardiac output. Because of this, the algorithm can give advice, and it can give advice or fail to give advice by mistake. What is really sought is to distinguish heart rhythms that are absent or hemodynamically weak from those that have sufficient cardiac output.

With the latest work in the field of impedance cardiography, measuring impedance cardiography (ICG) from the same two electrodes used to obtain the ECG and used to deliver energy to the patient Became possible. Conventionally, in order to measure ICG, a 4-band type electrode is required to achieve sufficient accuracy. By using electrodes already adopted for ECG, ICG can be easily measured as another signal and information source. ICG contains information related to the presence of cardiac output rather than electrical heart activity, and is therefore used to help make heart rhythm classification more accurate and consistent. Referring to the upper trace in FIG. 1, we can see an ECG example of a subject with normal sinus rhythm (SR). The lower trace shows a time-synchronized trace of the same individual ICG, differentiated with respect to time (wrt) (dz / dt). This dz / dt signal is more commonly used for analysis than the intact ICG itself, so the term ICG is used in the rest of this document to actually mean the dz / dt signal. Will be done. Wherever we refer to intact ICG as sensed from the patient's electrodes, this will be clearly stated. For reference, the first derivative of the raw ICG signal is obtained as follows:
dZ / dt = d [ZZ ₀ ] / dt (1)
Where Z is the raw impedance measured from the patient's chest and Z ₀ is the baseline of Z impedance.

  Here, even if the form of the dz / dt (ICG) signal is very different, it also has the property of repeating the pulsation by pulsing blood through the heart, thereby reducing the impedance of the chest. Note that it causes change. Comparing this with FIG. 2, it can be seen that blood flow is almost negligible during ventricular fibrillation (VF). Although the difference between VF and SR is obvious, ICG is really beneficial when comparing ventricular tachycardia (VT), where it is impossible to deliver shock, and those that can be shocked. FIG. 3 again shows the rhythmic pumping of blood flow obtained from a patient suffering from acute VT. In this case, there is no advice to give an un-synchronized shock. When this is compared with FIG. 4, lack of blood flow is seen again. Failure to shock the patient will result in death due to lack of blood flow to the brain. But before leaving these figures, note the electrocardiogram above both figures in FIGS. It can clearly be seen how difficult it is for any automated algorithm to distinguish between these. Finally, keep in mind that these traces were all taken under controlled circumstances, and even if the ICG traces are clear and stable, they can be It is not typical of what would be obtained when attempting to record an ICG from a patient suspected of having heart failure in the field.

  There are many scientific publications regarding the use of ICG to measure cardiac output. However, all of these publications do not mention one major problem that should be solved before ICG is used in real life. There are various ways to obtain the ICG signal. They are all involved in the variation signal applied from the detection electrode. This signal can be designed to either have a fixed voltage or have a fixed current. The effect the subject undergoing the test has on the signal is measured and the impedance of the subject is calculated. The component of this measurement is the impedance of blood in the heart. As the volume of this blood changes during the cardiac cycle, the measured impedance changes. Unfortunately, the measured impedance due to changes in the volume of blood in the heart is significantly less than the total impedance of the subject's torso. This means that ICG is perceived as a small change in the value of a much larger baseline impedance. Other factors also affect the measurement, such as volume changes due to inspiration and expiration. Even very little muscular activity and movement can affect the contact impedance of the electrodes and can significantly affect the measurement. All of these factors result in limiting the use of ICG to measure cardiac output to the laboratory or controlled condition.

  Many methods are known to those skilled in the art that can reduce the effects of these factors. Some methods relate to filtering, signal averaging, Fourier analysis, and differential impedance measurements. It describes a method for analyzing ICG as soon as it is obtained. Typically, they are involved in using a mathematical differentiation and integration process and attempt to collect cardiac output measurements from ICG. Figures 5 and 6 show the measurement of dz / dt peak and area under the C wave, which is reported to have a quantitative correlation with cardiac output. There are two parameters. FIG. 5 shows how various parts of the dz / dt wave type are labeled by conversion. Unfortunately, the reliability of these parameters and technology is somewhat low. Baseline impedance, heart structure, and the subject's blood vessels must all vary from individual to individual. All of these past attempts have common limitations, which employ a signal source that includes a lot of interference resulting from undesirable variables while they measure blood flow through the heart. It is that.

In accordance with the present invention, a method for determining whether an event of cardiac electrical activity results in a corresponding blood flow event, comprising:
Collect cardiac electrocardiogram (ECG) and impedance cardiography (ICG) simultaneously;
Examines the continuous cycle of the ECG and detects that at least one cycle of waveform features suggestive of cardiac electrical activity occurs continuously;
Each such detection is followed by a time period (search period),
Examining the ICG or the signal obtained therefrom within each of the search cycles, detecting the occurrence of waveform features indicative of blood flow ("corresponding waveform features") resulting from the occurrence detected in the ECG; and the detection Produces a signal that indicates the degree to which the ICG agrees with the ECG as a function measured with respect to the measured waveform features.
It consists of the process.

  The present invention further includes a circuit arranged to perform the method specified above and to selectively advise to shock depending on the value of the signal indicative of the degree of blood flow. An external defibrillator is provided.

  As mentioned above, the prior art includes many techniques that employ parameters measured from ICG. The intent is to measure the amount of cardiac output and subsequently decide whether to give treatment. Thus, any practical and theoretical attempt to provide a more accurate diagnosis by the AED algorithm will use this measurement in various ways and augment the measurement made from ECG.

  However, the novel method described below does not emphasize that the cardiac output or blood flow is measured very accurately. The principle of this method may not be immediately visible as it shows that it provides a general solution to the problem. But this method did just that.

  The essence of this method is related to “gating” the information provided by the ICG to that obtained from the ECG. There is no direct attempt to measure blood flow quantitatively with any accuracy. Rather, it aims to qualitatively determine whether there is any agreement between the cardiac events depicted by the ECG and the events presented by the ICG. With this new approach to ECG-ICG events, gating is very effective in distinguishing shockable VT from non-shockable VT in both human and animal subjects. It turns out that this approach is likely to be applicable to other situations such as atrial flutter / fibrillation and VF. Gating can be applied to any rhythm, and it should be appreciated that many parameters obtained from both ECG and ICG are used without departing from the scope of the present invention.

  Gating uses the initially processed ECG and ICG signals using methods well known to those skilled in the art. In the case of ICG, these remove as much interference, contamination and variation as possible while leaving the basic ICG intact. Unlike the prior art, however, this pretreatment can be done much more aggressively. This is because the present invention does not require accurate and quantitative measurement of cardiac output. So the pre-processing design has much more freedom to clean the signal, so that disturbances such as movement are almost totally eliminated, a solution that has never been possible using other approaches. is there. Overlapping ECG components and interference frequency bandwidth has always been a tedious dilemma for biomedical engineers. The electrical activity of the heart occurs much faster than the mechanical contraction, because the ICG component due to heart contraction and cardiac output results in a low frequency component bandwidth in the ICG. Means. This means that this dilemma is much worse for ICG than ECG. Although the constraints have been removed by much of the pre-processing, the conditions that can be used for the present invention provide a signal with a much higher signal / noise ratio than can be used in the prior art. This means that the end result is much more reliable, especially in emergency response situations “out of hospital”.

  FIG. 9 is a block diagram of an embodiment of the present invention implemented in an automatic external defibrillator (AED). With the exception of patient electrode 10, the components of a typical AED are well known and are not shown in the figure.

  The AED includes a general patient electrode 10, which is applied to the patient and obtains both ECG and ICG waveform signals simultaneously. The signal conditioning circuit 12 filters each signal together with a Butterworth reaction using an analog filter to a bandwidth of 3-20 hertz. Circuit 12 further differentiates the ICG to obtain dz / dt as the ICG signal for further analysis, and digitizes the ECG individually but simultaneously to differentiate the ECG signal. The digitized ECG and ICG signals are passed to feature extraction circuits 14 and 16 based on the respective microprocessors.

Circuit 14 tests the continuous ECG heartbeat cycle and detects each successive occurrence of a number of periodic waveform features E ₁ through E _N indicative of the heart's electrical activity. One such feature is the R wave, which is shown in FIG. Other features such as Q-waves may be detected and are well known to those skilled in the art.

The circuit 16 tests the heartbeat cycle (period) of the continuous ICG and detects that a number of periodic waveform features I ₁ to I _N each indicative of blood flow in the heart are continuously generated. However, the ICG waveform features I ₁ to I _N are not arbitrarily selected, each paired with one of the ECG waveform features E ₁ to E _N , and each pair E _n , I _n is (0 <n <N + 1) has an electromechanical relationship. This particular ECG waveform feature E _n is meant to bring ICG feature waveform I _n corresponding (in healthy persons of the heart). For the R wave in the ECG, the paired waveform feature in the ICG is the C wave, which is shown below in FIG. 7 for the continuous period of the ICG. To extract the characteristics of the R and C waves, a waveform detector is used separately for both signals, the ECG detector is optimal for R wave detection, and the ICG detector is optimal for C wave detection It has become.

The detected features are then sent to a temporal comparator 18. Thus each of the ECG waveform feature following the detection time of the period of E _n (search period) is defined, examine the ICG waveform for the presence of characteristic I _n became pair during the search cycle. The duration of the search cycle is calculated from heart rate-dependent measurements made on the ECG and is designed to reveal a pair of features (if any) within the time following the detected ECG features Yes. Thus, the duration of the search cycle will depend on the heart rate and the particular waveform feature selected. In this particular embodiment, the search period will be calculated as twice the QRS interval in the ECG.

When certain pair is detected, i.e., when the associated ECG features ICG characterized I _n Following E _n is found in the search cycle, E _n, the parameter in the measurement (below a pair of each feature of I _n Is called). Parameter is not to be arbitrarily selected, it is equivalent for features E _n and wherein I _n. Therefore, if the parameters in E _n if the width of the R-wave, equivalent parameters in I _n is the width of the C wave. The other pair of parameters is the ECG R wave height and the ICG C wave height, the area ratio under the R and Q waves in the ECG, and the area ratio under the C and X waves in the ICG. , And other parameter pairs that would be known to those skilled in the art. The parameters measured for each R wave in the example shown in FIG. 8 are RR intervals such as δR ₁ and δR ₂ up to the next R wave, and the equivalent parameters measured for each C wave are CC intervals such as ΔC ₁ and ΔC ₂ .

This process is applied to all features from E ₁ to E _N in each period of the ECG waveform, generating a paired set of parameters for each waveform period, X ₁ ^src to X _N ^src , where src Indicates the origin of the ECG or ICG parameter origin. Thus, X ₁ ^ECG indicates the value of parameter number 1 for ECG, and X ₁ ^ICG indicates the value of the ICG pair. If the paired feature is not found and therefore the corresponding ICG parameter cannot be measured, a large incorrect value is substituted.

Next, the parameter pairs X ₁ ^src through X _N ^src pass through a concordance estimator 20. In this embodiment, the estimator creates a linear sum of all contrasts of all parameter pairs.

であり、ここで、X₁はパタメーター対の識別子である。 For the specific parameters seen in Figure 8, the difference between the pair is:

Where X ₁ is the identifier of the parameter pair.

  In this particular embodiment, during the concordance, the parameter pairs are chosen so that their differences are very small, which means that when there is a match between the ECG and the ICG (the concordance), the Estimate Y is very Means that Y has a very large value when there is a low dissociation and a large error value contributes to poor correlation or there is a persistent dissociation. Therefore, Y indicates that the ICG lacks concordance with the ECG, and the larger the Y, the more concordance will be recognized (higher concordance indicates rhythmic blood flow). , It will support survival and the patient will be assessed as not requiring shock).

Finally, Estimate Y is selectively used by diagnostic algorithm 22 and the value of diagnostic algorithm 22 is ignored in various rhythms, but is outside the scope of this application when the rhythm is already classified as VT. In addition to some other criteria, the value is compared to a predetermined threshold. It is not advised to shock if the concordance rating is below the given VT threshold. So as a final eligibility, if:
Y ≥ E _th
Then it is advised to shock. Therefore, the AED shock circuit 24 advises whether to give a shock or not according to the value of Y.

  This technique is very effective in reducing false positives of algorithm 22. The result is the same when analyzing signals that contain a large degree of impedance disturbance. The use of this technique is believed to be useful for applications to rhythms other than VT, and it should be appreciated that this does not depart from the scope of the present invention.

  The techniques described above provide new qualitative techniques that are applied after the ICG is obtained and adjusted. The technology overcomes the problems described in connection with the prior art, and the provision of the method makes it possible to use ICG in real situations and not to shock the heart rhythm Therefore, it is possible to reliably identify what can give a shock.

  The present invention is not limited to the embodiments described herein, but can be modified and changed without departing from the scope of the present invention.

FIG. 1 is an example of an ECG signal from a normal sinus rhythm (SR) subject (top), shown with the corresponding time-synchronized ICG signal (bottom). FIG. 2 is an example of an ECG signal from a subject with ventricular fibrillation (VF) (upper) and is shown with the corresponding time-synchronized ICG signal (lower). Figure 3 is an example of an ECG signal from a ventricular tachycardia (VT) subject (upper), shown with the corresponding time-synchronized ICG signal (lower), which requires alternative treatment and is asynchronous Should not be shocked. Figure 4 is an example of an ECG signal from a ventricular tachycardia (VT) subject (upper), shown with the corresponding time-synchronized ICG signal (lower), which requires an urgently terminating shock. . FIG. 5 shows the measurement of the peak dz / dt parameter used to determine cardiac output. FIG. 6 shows the measurement of the area under the C wave, another parameter used to determine cardiac output. FIG. 7 shows the results of the waveform detection process for both the R wave in the ECG and the C wave in the dz / dtICG signal. FIG. 8 shows an example comparing ECG and ICG. FIG. 9 shows a block diagram of an embodiment of the present invention.

Claims (5)

A method for determining whether an event in the electrical activity of the heart leads to a corresponding blood flow event, comprising the following steps :
(A) collecting ECG of the heart (ECG) and heart beat diagram (impedance Karujiogura beam, ICG) simultaneously,
(B) examining the continuous heartbeat cycle of the electrocardiogram and detecting the continuous occurrence of a plurality of periodic waveform characteristics, each indicative of cardiac electrical activity;
(C) each such detected after a period ( "search period") the shall be specified step,
(D) at each of said search period, examine the heart beat view, the detected corresponding to the waveform characteristic of the electrocardiogram, and the detected occurrence of waveform characteristics in ECG pointing to blood flow caused by the waveform nature of the electrocardiogram Detecting, and
(E) for each cardiac cycle, the signal indicating the degree of concordance with the heartbeat view and ECG is below, i.e.
(F) for each set of corresponding features detected in step (d), measuring an equivalent parameter for each feature of the set; and
(G) Summing the differences between each set of measured parameters of the corresponding attribute
A method comprising the step of generating by: 1 different periodic waveform characteristics of ECG is R-wave, and the waveform characteristics corresponding in heartbeat diagram is C wave, the method of claim 1. R-R interval is measured with respect to the waveform characteristics of the ECG detected, and C-C distance is measured with respect to the waveform characteristics of the detected heart beat diagram method of claim 2, wherein. Search period is calculated from measurements made on the ECG, such measurements depends on the heart rate, any one method according to claim 1-3. An external defibrillator comprising a network arranged to carry out the method according to any one of claims 1 to 4 and to selectively signal an impact depending on the degree of concordance. , Defibrillator.

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